Background of the Invention
[0001] This invention relates to ultrasound imaging systems, and in particular to improved
methods for imaging nonlinear contrast agents with such systems.
[0002] Nonlinear contrast agents are described for example by V. Uhlendorf, et al., in "Nonlinear
Acoustical Response of Coated Microbubbles in Diagnostic Ultrasound" (1995 Ultrasonic
Symposium, pp. 1559-1562). Such agents possess a fundamental resonant frequency. When
they are insonified with high intensity ultrasonic energy at this fundamental frequency,
they radiate ultrasonic frequency at a harmonic of the fundamental frequency. Such
contrast agents are often used to highlight regions containing blood loaded with the
contrast agent. For example, in the case of a blood-filled chamber of the heart, the
borders of the chamber can be distinguished more easily when contrast agent is used.
Since the contrast agent generates harmonic ultrasound energy, echoes from tissue
(containing no contrast agent) at the fundamental frequency may be eliminated by filtering
at the receive beamformer.
[0003] Typically, such agents are used with an imaging system having a transmit beamformer
that transmits ultrasonic energy at the fundamental frequency and a receive beamformer
responsive to the harmonic. In order to image the contrast agent clearly, it is known
to reduce energy at the harmonic in the transmit beam, and to reduce sensitivity of
the receive beamformer to energy at the fundamental.
[0004] In the past, this has been done by using a burst of square or sine waves to form
the transmit beam, and by using appropriate band pass or high pass filters in the
receive beamformer. Though a large pulse count reduces energy at the harmonic, it
reduces time resolution of the pulse, and therefore spatial resolution of the resulting
image.
[0005] The present invention is directed to further improvements that enhance the imagining
of such nonlinear contrast agents.
Summary of the Invention
[0006] This invention relates to improvements to a method for imaging a target, as described
in claims 4 and 6. The method comprises the steps of (a) transmitting ultrasonic energy
at a fundamental frequency and (b) receiving reflected ultrasonic energy at a harmonic
of the fundamental frequency.
[0007] According to further aspects of the present invention there is provided an ultrasonic
imaging system as described in claim 1 and claim 7.
[0008] According to a further aspect of this invention, the transmitting step includes the
step of transmitting ultrasonic energy in power bursts, each power burst comprising
a respective envelope shape, the envelope shapes rising gradually to a respective
maximum value and falling gradually from the respective maximum value. This arrangement
can reduce harmonic energy in the power burst.
[0009] According to a further aspect of this invention, the transmitting step includes the
step of generating a transmit waveform and filtering the transmit waveform with a
filter adapted to reduce ultrasonic energy in the transmit waveform at the harmonic
of the fundamental frequency to at least -30 dB with respect to the fundamental frequency.
[0010] According to a further aspect of this invention, the transmitting step includes the
step of generating a transmit waveform with a programmable waveform generation such
that ultrasonic power in the transmit waveform at the harmonic of the fundamental
frequency is reduced by at least -30 dB with respect to ultrasonic power in the transmit
waveform at the fundamental frequency.
[0011] According to a further aspect of this invention, the transmitting step includes the
step of focusing ultrasonic energy in a transmit beam having a line focus.
[0012] According to a further aspect of this invention, the transmitting step includes the
step of focusing ultrasonic energy in a transmit beam having an elongated high power
region by focusing at least first selected frequency components from at least a first
plurality of transducer elements at a first range and focusing at least second frequency
components from at least a second plurality of transducer elements at a second range.
[0013] Other aspects of the invention relate to the use of switched filters in the transmitting
step.
[0014] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target during an imaging session, said method comprising
the following steps, (a) transmitting ultrasonic energy in power bursts at a fundamental
frequency into the target, said target being free of contrast agent throughout the
entire imaging session, each power burst comprising a respective envelope shape, each
envelope shape rising gradually to a respective maximum value and falling gradually
from the respective maximum value, and (b) receiving reflected ultrasonic energy from
the target at a harmonic of the fundamental frequency.
[0015] Optionally, said power bursts may be characterized by a power level at the harmonic
which is reduced by at least 30 dB with respect to ultrasonic power in the power burst
at the fundamental frequency.
[0016] Optionally, said power bursts may be characterized by a power level at the harmonic
which is reduced by at least 40 dB with respect to ultrasonic power in the power burst
at the fundamental frequency.
[0017] Preferably, the method further comprises, (c) generating a transmit waveform, (d)
filtering the transmit waveform with a filter adapted to reduce the ultrasonic energy
in the transmit waveform at the harmonic of the fundamental frequency by at least
30 dB with respect to the fundamental frequency, wherein at least one of the power
bursts is responsive to the transmit waveform.
[0018] Advantageously, the method further comprises, (c) generating a transmit waveform
with a programable waveform generator such that ultrasonic power in the transmit waveform
at the harmonic of the fundamental frequency is reduced by at least -30 dB with respect
to ultrasonic power in the transmit waveform at the fundamental frequency, wherein
at least one of the power bursts is responsive to the transmit waveform.
[0019] Optionally, each power burst may be characterized by a respective frequency spectrum
having a respective center frequency, a respective peak amplitude, and a respective
bandwidth, the bandwidth of each power burst being at least about 30% of the respective
center frequency at points -6.8 dB with respect to the respective peak amplitude,
said frequency spectra reduced at the harmonic by more than 30 dB with respect to
the peak amplitude.
[0020] Advantageously, the bandwidth of each power burst is at least about 50% of the respective
center frequency at points -6.8 dB with respect to the respective peak amplitude.
[0021] Advantageously, each power burst is characterized by a respective frequency spectrum
having a respective peak amplitude near the fundamental frequency, said frequency
spectrum reduced within a first bandwidth greater than or equal to ±X% of the harmonic
of the fundamental frequency by more than Y dB with respect to the peak amplitude,
where X is equal to 5 and Y is equal to 30.
[0022] Optionally, X may be equal to 10.
[0023] Optionally, X may be equal to 15.
[0024] Optionally, X may be equal to 10 and Y may be equal to 50.
[0025] Optionally, X may be equal to 15 and Y may be equal to 50.
[0026] Preferably, each frequency spectrum has a respective center frequency, a respective
peak amplitude, and a respective second bandwidth, the second bandwidth of each frequency
spectrum being at least about 30% of the respective center frequency at points -6.8
dB with respect to the respective peak amplitude.
[0027] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target during an imaging session, said method comprising
the following steps, (a) transmitting ultrasonic energy at a fundamental frequency
into the target in a transmit beam having a line focus, said target being free of
contrast agent throughout the entire imaging session, and (b) receiving reflected
ultrasonic energy from the target at a harmonic of the fundamental frequency.
[0028] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target during an imaging session, said method comprising
the following steps, (a) transmitting ultrasonic energy at a fundamental frequency
into the target in a transmit beam having an elongated high power region by focusing
at least first selected frequency components from at least selected transducer elements
at a first range and focusing at least second frequency components from at least selected
transducer elements at a second range, said target being free of contrast agent throughout
the entire imaging session, and (b) receiving ultrasonic energy from the target at
a harmonic of the fundamental frequency.
[0029] According to a further aspect of the present invention, there is provided an ultrasonic
imaging system comprising a transmit beamformer operative to transmit energy at a
fundamental frequency, and a receive beamformer responsive to ultrasonic energy at
a harmonic of the fundamental frequency, having an improvement comprising means, included
in the transmit beamformer, for switching a plurality of voltages to form a bipolar
transmit waveform, and a filter, responsive to the bipolar transmit waveform to suppress
ultrasonic energy at the harmonic to form a filtered bipolar transmit waveform, said
filtered bipolar transmit waveform characterized by a power level reduced by at least
30 dB at the harmonic as compared to the fundamental frequency.
[0030] Optionally, the filter may provide at least 10 dB suppression at the harmonic.
[0031] Optionally, the power level may be reduced by at least 40 dB at the harmonic as compared
to the fundamental frequency.
[0032] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target comprising the following steps, (a) switching
a plurality of DC voltages to form a bipolar transmit waveform, (b) filtering the
bipolar transmit waveform to form a filtered bipolar transmit waveform characterized
by a fundamental and a harmonic frequency, said harmonic frequency reduced with respect
to the fundamental frequency by at least 30 dB, (c) transmitting ultrasonic energy
into a target in response to the filtered bipolar transmit waveform, and (d) processing
echo ultrasonic energy from the target at the harmonic for display.
[0033] Optionally, the power of the filtered bipolar transmit waveform at said harmonic
frequency may be reduced with respect to the fundamental frequency by at least 40
dB.
[0034] According to a further aspect of the present invention, there is provided a method
ultrasonically imaging a target, said method comprising the steps of (a) transmitting
ultrasonic energy at a fundamental frequency and (b) receiving reflected ultrasonic
energy at a harmonic of the fundamental frequency, having an improvement wherein step
(a) comprises the step of (a1) filtering a transmit signal in a first mode of operation
with a filter adapted to pass energy at the fundamental frequency and to suppress
energy at the harmonic, and (a2) controlling a switch to selectively bypass the filtering
step in a second mode of operation.
[0035] According to a further aspect of the present invention, there is provided an ultrasonic
imaging system comprising a transducer, a transmitter coupled to the transducer and
operative to transmit ultrasonic energy at a fundamental frequency, and a receiver
responsive to ultrasonic energy at a harmonic of the fundamental frequency having
an improvement comprising first and second signal paths coupled to the transmitter
and the transducer, a filter included in the first signal path, said filter adapted
to suppress ultrasonic energy at the harmonic, and a switch coupled to the first and
second signal paths, said switch operative to route signals from the transmitter to
the transducer through a selectable one of the first and second signal paths.
[0036] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target comprising the following steps, (a) transmitting
ultrasonic energy at a fundamental frequency along a plurality of transmit lines,
(b) receiving ultrasonic energy at a harmonic of the fundamental frequency along a
first plurality of receive lines, wherein a second plurality of said first plurality
of receive lines are formed in response to one of said transmit lines.
[0037] Optionally, the target may comprise a contrast agent.
[0038] According to a further aspect of the present invention, there is provided a method
for ultrasonically imaging a target, said method comprising the following steps, (a)
transmitting ultrasonic energy at a fundamental frequency into the target in a transmit
beam having at least two focal regions, and (b) receiving ultrasonic energy from the
target at a harmonic of the fundamental frequency.
[0039] Optionally, said ultrasonic energy may be transmitted in power bursts characterized
by a power level at the harmonic which is reduced by at least 30 dB with respect to
ultrasonic power in the power burst at the fundamental frequency.
[0040] Preferably, said target is free of contrast agent throughout an entire imaging session.
Brief Description of the Drawings
[0041]
Figure 1 is a block diagram of an ultrasonic imaging system suitable for use with
the method of this invention.
Figure 2 is a block diagram of a transmit beamformer suitable for use in the system
of Figure 1.
Figure 3 is a graph of a Gaussian pulse in the frequency domain.
Figure 4 is a graph of a waveform corresponding to the Gaussian pulse of Figure 3
in the time domain.
Figure 5 is a graph of a focusing profile suitable for an axicon focus.
Figure 6 is a schematic representation of a compound focus arrangement.
Figure 7 is a graph showing high and low frequency wavefronts.
Figure 8 is a block diagram of a second transmit beamformer suitable for use in the
system of Figure 1.
Figure 9 is a block diagram of a third transmit beamformer suitable for use in the
system of Figure 1.
Figures 10, 11, and 11a are block diagrams of portions of transmit beamformers that
incorporate preferred embodiments of this invention.
Figure 12 is a waveform diagram illustrating operation of the beamformers of Figures
10-11a.
Figures 13-16 are graphs illustrating the temporal and frequency characteristics of
waveforms produced by the beamformers of Figures 10-11a.
Figure 17 is a graph illustrating a filter transfer function suitable for use in the
beamformers of Figures 10-11 a.
Figures 18-23 are block diagrams of alternative filter circuits suitable for use with
ultrasonic harmonic imaging systems.
Detailed Description
[0042] The preferred examples described below are designed to reduce harmonic energy in
the transmitted beam, and to provide an improved spatial distribution of fundamental
energy in the transmitted beam. Figure 1 shows generally an ultrasonic imaging system
10 which can be used to practice the method of this invention.
[0043] The system 10 includes a transmit beamformer 12 that supplies high voltage transmit
waveforms via a multiplexer 14 to a transducer array 16. The transducer array 16,
which can be any suitable type, generates an ultrasonic transmit beam in response
to the transmit waveforms, and this transmit beam propagates outwardly through the
subject 18 being imaged. In this case, the subject being imaged includes a nonlinear
contrast agent 20, such as that described above. Any suitable contrast agent may be
used, as long as it absorbs ultrasonic energy at a first frequency and radiates ultrasonic
energy at a second frequency, different from the first frequency. In this example,
the first frequency is referred to as the fundamental frequency, and the second frequency
is a harmonic of the first frequency. As used herein, "harmonic" is intended broadly
to include sub-harmonics and fractional harmonic energy (e.g. 1/2 or 3/2 of the fundamental),
as well as higher harmonics (e.g. 2 or 3 times the fundamental).
[0044] Ultrasonic energy radiated by the nonlinear contrast agent 20 at the harmonic frequency
is received by the transducer array 16, focused by the receive beamformer 22, and
displayed as an image by a display processor (not shown). As described above, the
receive beamformer 22 includes conventional filters to substantially prevent reflected
ultrasonic energy at the fundamental frequency from being imaged.
[0045] Turning now to Figure 2, this figure shows a block diagram of a first preferred embodiment
40 of the transmit beamformer of Figure 1. As shown in Figure 2, the transmit beamformer
40 includes N channels, one for each of the transducers of tne transducer array 16
(Figure 1). Each channel includes a delay memory 42, a waveform memory 44, and a delay
counter 46 (Figure 2). The delay memory 42 includes 256 words 48, one for each possible
steering angle or ultrasound transmit scan line. Each word 48 of the delay memory
42 is set equal to a negative number equal to the number of clock cycles on the clock
signal line 50 that elapse between a start of line signal on line 54 and the first
non-zero value of the associated waveform. For simplicity, it is assumed that zero
is defined as a word 48 having the most significant bit equal to one and all other
bits equal to zero. Hence, the most significant bit becomes an enable signal for the
waveform memory 44.
[0046] The waveform memory 44 in this embodiment stores a single waveform in digital form,
which is used for all transmit scan lines. The waveform memory 44 can include for
example 64 or 128 successive 8 bit words. The magnitude of each 8 bit word corresponds
to the voltage amplitude at the respective position in the waveform. When the waveform
memory 44 is read with a 40 MHz clock on the line 50, the resulting sequence of digital
values defines a waveform approximately 1.6 to 3.2 microseconds in duration.
[0047] The delay memory 42 is not required, but it reduces memory requirements for the waveform
memory 44. This is because the delay memory 42 eliminates the need to store a large
number of leading zeros when the ultrasound line is steered at a large angle.
[0048] In use, each channel responds to a scan line selection signal on line 52 by loading
the word 48 for the selected scan line into the delay counter 46. The delay counter
46 responds to a start of scan line signal on line 54 by incrementing the stored value
with each cycle of the 40 MHz clock on line 50. When the counter 46 increments to
zero, it enables the waveform memory 44. Subsequently generated values of the counter
46 (incrementing now from zero upwards) become address values for the waveform memory
44. As each word of the waveform memory 44 is addressed, the corresponding 8 bit word
is read and applied to a digital to analog converter 56.
[0049] The analog output signal of the converter 56 is passed through a low pass filter
such as a Bessel filter 58 to reduce sampling effects and then to an amplifier 60.
The output of the amplifier 60 can be passed through an additional low pass filter
62 to improve harmonic rejection. The output of the low pass filter 62 is the transmit
waveform discussed above that is applied to the respective transducer via the multiplexer
14 (Figure 1). The low pass filters 58, 62 preferably provide a sharp cut-off with
a low stop band level in order substantially to eliminate ultrasonic energy in the
transmitted pulse at the harmonic frequency.
[0050] The transmit beamformer 40 utilizes values for the waveforms stored in the waveform
memory 44 and the delays stored in the delay memory 42 that enhance insonification
of the nonlinear contrast agent in the subject.
[0051] The waveform stored in the waveform memory 44 is shaped to suppress ultrasonic energy
in a wide pass band centered at the harmonic frequency. For example, the spectrum
of the desired pulse can be designed on a computer 64. Figure 3 shows the frequency
spectrum of one suitable pulse 70 which is centered at the fundamental frequency of
2.5 MHz and is generally Gaussian in shape. The particular Gaussian shape shown in
Figure 3 has an amplitude reduced by 71 dB at 3.71 MHz. The bandwidth of the pulse
70 is 30% of the center frequency, measured at points -6.8 dB with respect to the
peak amplitude. Such a pulse will be referred to herein as a 30% BW Gaussian pulse.
Note that the pulse 70 has substantially no energy at 5 MHz, the first harmonic of
the fundamental frequency. This invention is not limited to use with Gaussian pulses,
and a wide range of spectra can be used.
[0052] Once the desired pulse has been designed, an inverse fast Fourier transform is then
performed to generate the corresponding time domain waveform. Figure 4 shows a waveform
80 which corresponds to the pulse 70 of Figure 3. Note that the waveform 80 includes
an oscillating component having a frequency of about 2.5 MHz. This oscillating component
is shaped by an envelope 82. The envelope 82 rises graduaily from zero amplitude to
a maximum amplitude, and then falls gradually from the maximum amplitude back to zero
amplitude. Thus, the envelope 82 is quite different from the envelope for a switched
pulse train, which is substantially rectangular in shape. The gradually increasing
and gradually decreasing envelope 82 of Figure 4 brings with it the advantage of reduced
ultrasonic energy at harmonics of the fundamental frequency.
[0053] Once a waveform such as the waveform 80 of Figure 4 has been designed, the waveform
80 can be coded into binary samples at a suitable sample rate and then stored in the
waveform memory 44. The waveform memory 44 may be a read only memory, in which case
the computer 64 may not be required to be connected to the transmit beamformer 40.
Alternately, the waveform memory 44 may be a volatile memory which is programmed at
power-up initialization by the computer 64. The computer 64 may perform any desired
subset of the pulse designing steps described above. Typically, the desired pulse
may be one of several selectable pulses included in a menu for user choice.
[0054] When the waveform in the waveform memory 44 is designed as described above, the result
is a broad band waveform in the waveform memory 44 which simultaneously has substantially
no radiated energy in a broad band centered on the harmonic. In the example of Figures
3 and 4, substantially no ultrasonic energy is radiated at frequencies above 4 MHz,
or in a bandwidth of ± 1 MHz with respect to the first harmonic (5 MHz). Preferably,
the energy component at the harmonic is more than 30 dB reduced with respect to the
magnitude of the fundamental frequency, and ideally is reduced by more than 40 dB.
[0055] Of course, it is not necessary to define the waveform 80 initially in the frequency
domain. A Gaussian pulse can be defined in the time domain. Furthermore, the envelope
need not be Gaussian, it may be some other window function such as a Hamming pulse,
a modified Gaussian pulse, or any other suitable pulse. In some applications it may
be preferable to use a narrow bandwidth pulse and thereby achieve a very high reduction
of energy at the harmonic, since the harmonic of the lower bandedge is well above
the upper bandedge. On other occasions it may be preferable to use a wider bandwidth
pulse, for example, to obtain better axial (temporal) resolution. In this case, somewhat
reduced reduction of energy at the harmonic may be accepted.
[0056] An alternative approach is to design the pulse 70 to ensure that substantially no
energy is transmitted above 1.5 times the center frequency of the intended fundamental
pulse (3.75 MHz in this case). It is preferable to limit low frequency energy in the
transmitted pulse so that the harmonic energy associated with this frequency does
not fall within the spectrum of the transmitted pulse. If the cut off frequency is
3.75 MHz, there should be very little transmitted energy below 1.875 MHz.
[0057] In designing the pulse 70 and the waveform 80, the Gaussian waveform may be passed
through a high order, low pass filter to eliminate all harmonic energy. This filtering
may be done off line in the computer 64.
[0058] Optimum imaging of the nonlinear contrast agent is obtained when the transmit beam
insonfies the agent at power levels within a desired range. Power levels below this
range may not be sufficiently high to cause the nonlinear contrast agent to radiate
at the harmonic frequency. Power levels above this range may destroy the contrast
agent prematurely. Additionally, since there are FDA limits on ultrasound intensity,
a sharply focused transmit beam is not optimal. Such a sharply focused beam provides
a high intensity (near the FDA limits) at the focus, but an intensity that is undesirably
low at many other points along the associated receive scan line.
[0059] The receive beamformer 22 preferably receives samples along an entire scan line for
each transmit event. For this reason, it is preferable that the region of insonification
within the desired power level range be extended over a substantial portion of the
length of the receive scan line. Thus, it is preferable that the intensity of the
transmitted ultrasonic energy be substantially uniform and at a high level throughout
the field of interest (which is typically a large fraction of the displayed depth).
[0060] The delay memory 42 preferably stores delay values to provide a controlled spread
to the beam intensity in a way to optimize imaging of the contrast agent. Also, by
making the intensity of harmonic energy received at the receive beamformer 22 more
uniform throughout the field of interest, the levels of harmonic back scatter may
be better controlled, resulting in manageable voltage swings at the receiver input.
[0061] The delay values stored in the delay memory 42 are selectively chosen to spread the
beam along the current ultrasound line. One way to accomplish this is to use the well-known
axicon focusing arrangement, as described, for example by C. Burckhardt in "Ultrasound
Axicon: A Device for Focusing over a Large Depth" (J. Acoust. Soc. of Am.,
54, 6, pp. 1628-1630 (1973)). The axicon focusing arrangement may utilize a focusing
profile as shown in Figure 5. Typically, this focusing profile provides a near focal
limit corresponding to a circular arc centered on the near focal limit. Typically,
the delay profile extends linearly outwardly from this circular arc to some outer
limit, as shown in Figure 5.
[0062] The objective is to spread the ultrasound energy throughout a region of the target,
and many different delay profiles may accomplish this result. For example, the delay
profile may be slightly curved, with a nonlinear variation of focal point with respect
to transducer element position. There may be an outer focal limit, in which case the
delay profile can include a circular portion at the ends of the array.
[0063] In many applications, it will be desirable to select the delay values in the delay
memory 42 such that at least first frequency components of the transmit beam from
at least a first plurality of transducers are focused at a first, shorter range, and
that at least second frequency components of the transmit beam from at least a second
plurality of transducers are focused at a second, longer range. One example is shown
in Figure 6, where substantially all of the ultrasonic energy from the transducers
16a at the end portions of the transducer array 16 are focused at a single longer
range X1, and substantially all of the ultrasonic energy from the transducers 16b
at central portions of the array are focused at a single, shorter range X2. By properly
selecting the delay values, a line focus or a multiple-point compound focus may be
obtained. When a line focus is used, the line may be straight or curved.
[0064] Another approach begins with focal delays required for a chosen focal point in the
conventional manner. A random delay error is superimposed on these focal delays to
smear or defocus the resulting beam. The greater the degree of defocusing, the more
spread out the beam is. Preferably, a user control is provided to allow the user to
vary the degree of defocusing by increasing the relative level of the defocusing delays.
Also, it is preferable to increase the transmitted energy level to partially compensate
for the loss of peak field intensity due to defocusing, either in an automatic (internally
programmed) manner or under user control. The defocusing hardware can consist of a
modified version of aberration correction hardware in which the delay corrections
are pre-programmed random numbers rather than values which are continuously updated,
for example by means of cross-correlating the waveforms from adjacent elements.
[0065] Conventional imaging at the fundamental frequency using an axicon or defocused beam
is known to produce side lobes. However, such side lobes are not anticipated to create
substantial problems in this application, particularly if the side lobes are below
the harmonic activation threshold intensity and they therefore do not contribute to
the generation of harmonic energy. Full dynamic receive focusing is preferably performed
in the receive beamformer 22 to reduce the effect of side lobes in the transmit beam
further.
[0066] Regardless of the precise configuration of the pulse 70 and the waveform 80, the
waveform 80 preferably provides more uniform field intensity through a usefully extended
depth of field. This results in more uniform generation of harmonic energy by the
contrast agent and possibly a higher overall signal to noise ratio since more of the
field is being unisonified at a sufficiently high power level to cause the contrast
agent to radiate harmonic energy, but at a sufficiently low power level to prevent
unnecessarily rapid destruction of the contrast agent.
[0067] If desired, the axicon focus may be obtained with a lens. Also, an axicon focusing
scheme may be used in the elevation direction, if it is desired to increase the dimension
of the insonified region in that direction.
[0068] The transmit beamformer 40 of Figure 2 is quite similar to the beamformer shown in
Figure 13 of U.S. Patent 5,608,690, and the techniques described above relating to
Gaussian waveforms modified to provide a line focus can be performed in the manner
described in the above-identified application. Note in particular pages 23 and 24
of the above-identified application as filed, which expressly relate to optimized
transmit beamformers for use with nonlinear contrast agents. With this approach, a
plurality of transmit waveforms are provided, each for a respective one of the transducers
of the transducer array. This plurality of transmit waveforms includes a central transmit
waveform associated with a central one of the transducers. As explained in the above-identified
patent application in detail, the central transmit waveform preferably comprises a
lower frequency component and a higher frequency component, and a lower frequency
component of the central transmit waveform occurs earlier in time than the higher
frequency component of the central transmit waveform, as shown in Figure 7. Figure
7 corresponds to Figure 11 of above-identified U.S. Patent 5,608,690, and that application
can be referenced for additional information regarding these figures. When the system
of U.S. Patent 5,608,690 is adapted for use with this invention, it is preferred that
the frequencies along the line focus all be near the fundamental frequency to insonify
the non-linear contrast agent effectively.
[0069] Additionally, the transmit beamformer described in Cole, et al., U.S. Patent Application
Serial No. 08/286,652, filed August 5, 1994, and in U.S. Patent Application Serial
No. 08/432,056, filed May 2, 1995, can be adapted for use with this invention. Once
the desired output is defined as described above in terms of very low harmonic signal,
one can then define the ideal output signal in the frequency domain and then convert
it to the time domain. This time domain signal can then be divided by the carrier
to obtain the desired envelope using complex shapes for both the time domain signal
and the carrier. This combination of envelope and carrier can then be programmed into
the transmit waveformer, using the parameters of attached Appendix 1. Appendix 1 provides
parameters for both B-mode and Flow Mode. Appendix 3 provides a revised set of transmit
beamformer parameters, and Appendix 4 provides a preferred set of transmit beamformer
parameters adapted for use with the Acuson 3V2C transducer probe.
[0070] The envelope is sampled at a relatively low frequency, and as a result of imperfections
in real implementations, remnants of harmonics relating to the sampling frequency
of the carrier and the base band signal may appear in the final result.
[0071] In this example, harmonic energy at the second harmonic from the contrast agent is
imaged using the receive beamformer described in Wright, et al. U.S. Patent Application
Serial No. 08/286,658, filed August 5, 1994, and in U.S. Patent Application Serial
No. 08/432,615, filed May 2. 1995, (issued as U.S. 5685308). This receive beamformer
can be programmed using the parameters of attached Appendix 2.
[0072] For example, the transmit beamformer of U.S. Patent Applications Serial Nos. 08/286,652
and 08/432,056 can be operated with a nominal center frequency FO equal to 5.0 MHz,
a transmit carrier frequency F
c equal to 2.5 MHz, and a Gaussian envelope having a 50% bandwidth at -6.8 dB with
8/4 envelope sampling.
[0073] Figure 8 shows another transmit beamformer 100 that can be used in the ultrasound
imaging system 10. The beamformer 100 includes a pulse generator 102 which supplies
a burst of pulses to a low pass filter 104. In this case, the pulse generator 102
switches between a selectable high voltage DC level and ground. The duration of the
pulses and the number of pulses in the burst are controllable, as described, for example,
in U.S. Patent No. 4,550,067 (Maslak, et al.).
The low pass filter 104 is designed as described above to substantially eliminate
energy at the harmonic. The low pass filter 104 can be an analog filter such as a
suitable Bessel or Chebyshev filter.
[0074] Figure 9 shows another transmit beamformer 120 that can be used in the system 10
of Figure 1. The transmit beamformer 120 includes a pulse generator 122 which supplies
pulses to a low pass filter 124. The output of the low pass filter is supplied to
a high voltage amplifier 126. Because the low pass filter 124 is applied prior to
the amplifier 126, the low pass filter 124 can be designed with smaller components
and hence can be higher order and more effective in suppressing harmonic energy.
[0075] It should be noted that conventional transducer arrays have a finite bandwidth, such
as 75% at the -6 dB levels. Considering the example where the fundamental frequency
is 2.5 MHz and the harmonic frequency is 5 MHz, the transducer will typically be centered
between the transmit and receive frequencies (as for example at 3.75 MHz), with a
relatively high bandwidth. Notice that when this transducer is operated at 2.5 MHz
with a symmetrical band shape, the transducer will skew the transmitted spectrum toward
higher frequencies. In the design of the transmitted pulse, the spectrum should preferably
be modified to take account of the skewing effect of the finite bandwidth effects
of the transducer and the fact that the transducer is working away from its center
frequency in transmit.
[0076] Of course, the techniques described above can be used in systems 10 which provide
apodization in the normal manner. If desired, apodization profiles can be modified
if experience shows that the contributions from the end transducer elements (which
are focused at deep ranges) are too attenuated. In this case, it may be preferable
to increase the weighting at the end elements to compensate for this effect to some
extent. By operating the end transducer elements at higher power levels than central
transducer elements, more nearly uniform power levels are obtained at various ranges
in the tissue being imaged.
[0077] A further modification is to use fewer transmit lines than receive lines. Since contrast
agent tends to be consumed by the insonification process, it is preferable to reduce
the number of transmit lines by reducing the frequency of firings and/or the spatial
density of lines. Reduced firings and density can be achieved by firing one fourth
the number of transmit lines and forming four synthetic receive lines closely spaced
around each transmit line, which may be slightly defocused if required. Wright, et
al. U.S. Patent Application Serial No. 08/418,640, filed April 7, 1995, (issued as
U.S.5667373) discloses synthetic line systems that can be adapted for this purpose.
Furthermore, frames of low intensity ultrasound may be interleaved with high intensity
frames.
[0078] Multiple transmit zone firing (compound focus) may also yield a better result by
spreading the beam between two selected focal regions. These techniques can be implemented
on the transmit beamformer described in U.S. Patent Application Serial No. 08/286,652,
as described above.
[0079] It has been discovered that bipolar waveforms derived from switched DC levels can
be filtered to provide effective suppression of ultrasonic energy at the harmonic.
This can represent a substantial advantage, because bipolar, switched DC pulse sequences
can be generated in a relatively inexpensive beamformer.
[0080] Figure 10 shows a block diagram of one channel of a transmit beamformer 200 that
utilizes such bipolar switched DC transmit waveforms. As shown in Figure 10, each
channel of the transmit beamformer 200 includes a binary waveform generator 202 that
responds to inputs from an input clock, a select line defining the number of waveform
cycles to be included in each pulse of energy, and a start input from a focal delay
memory 204 that is in turn responsive to an acoustic line select input. Once the appropriate
acoustic line has been selected, the focal delay memory 204 provides a start signal
to the binary waveform generator 202 at the appropriate time, and the binary waveform
generator 202 generates two output waveforms, which are 180° out of phase in this
example.
[0081] These two waveforms are applied to respective pulse amplifiers 206, 208. Each of
the pulse amplifiers 206, 208 responds to a high voltage input which can be switched
to one of a plurality of levels such as 10, 20 and 50 volts in this example. The pulse
amplifiers 206, 208 operate with positive and negative high voltage rails, respectively.
Typically, each pulse amplifier 206 includes a transistor circuit used to switch the
high voltage through the pulse amplifier 206, 208 to the output of the amplifier 206,
208. Each pulse amplifier outputs an amplified binary waveform, and the waveforms
are summed at a summing node prior to being applied as an input to an analog lowpass
filter 210. The signal applied as an input to the analog lowpass filter is a bipolar,
switched DC transmit waveform. The output of the analog lowpass filter 210 is a filtered
bipolar transmit waveform, which is applied to an ultrasonic transducer element 214
via a protection circuit 212. The protection circuit 212 is included to protect the
receive electronics from high voltage transmit pulses. This circuit is typically based
on a diode clamping circuit. Returning ultrasonic echoes from the target are converted
by the transducer element 214 into electrical signals that are passed via the protection
circuit 272 to a receiver (not shown), that typically includes a receive beamformer.
[0082] The analog lowpass filter 210 may be of any standard type. The filter 210 may comprise
various resistors, inductors, and capacitors, and may include Bessel, Butterworth
or Chebyshev filters, for example. Preferably, the filter 210 achieves approximately
20 dB of suppression at the second harmonic (two times the fundamental frequency).
Ideally, the filter 210 may achieve a far higher degree of suppression. This may be
achieved by using a high order filter, or a high suppression filter such as a Chebyshev
filter. If desired, a multipole filter or a band pass filter can be used. In some
applications, the components of the analog lowpass filter 210 are made switchable
so that the cutoff frequency of the filter 210 can be varied according to the frequency
characteristics of the transducer element 214 being used. This switching may be accomplished
using relays or semiconductor analog switches such as those supplied by Supertex as
HV2 type switches.
[0083] Although the filter 210 has been described above with respect to passive components,
it should be understood that the filter 210 may be implemented using active filter
circuits, including operational amplifiers for example. Such active filter circuits
are well-known in the art, and are described for example in Horowitz and Hill,
The Art of Electronics, Chapter 4 (Cambridge University Press, 1984).
[0084] Unipolar pulse sequences can also be formed using circuitry similar to that described
in Maslak U.S. Patent 4,140,022, which provides pulses having controllable amplitude,
period, and pulse count. See also the description of pulse sequence transmitters in
IEEE 1980 Ultrasonic Symposium, pp. 757-762 (Karrer, et al. "A Phased Array Acoustic
Imaging System for Medical Use").
[0085] It is not required in all cases that the lowpass filter operate on the high voltage
transmit waveform. An alternative beamformer 220 (Figure 11) sums the two chopped
DC output signals of a binary waveform generator 222 at a summer 223, and applies
this summed signal as an input to a lowpass filter 224. The output of the lowpass
filter 224 is applied to an adjustable gain amplifier 226 which amplifies the filtered
signal to a voltage level appropriate for application to the transducer element 230
via the protection circuit 228. This approach allows the waveform to be generated
and filtered at a relatively low voltage. This allows components rated at a lower
voltage to be used in the filter 224, which may provide an important cost reduction.
[0086] As another attemative, the lowpass filter 210, 224.may.include two components, one
for each of the unipolar components of the transmit waveform prior to the point in
the signal path where they are summed. See Figure 11a. where the two components of
the lowpass filter are shown at 232, 234
[0087] Figure 12 provides waveforms that illustrate the operation of the transmit beamformers
200, 220. As shown in Figure 12, the waveforms 240, 242 represent the output waveforms
from the binary waveform generator 202, 222. Note that the positive excursions of
the waveform 240 are out of phase by 180° with respect to the negative excursions
of the waveform 242. The waveforms 240. 242 are best considered as unipolar components
of the bipolar transmit waveform. The summation of the waveforms 240, 242 is shown
at waveform 244. This summed waveform is bipolar in that it includes both positive
and negative components, and is generated as described above as a sum of switched
DC signals. The waveform 244 represents the bipolar transmit waveform that is applied
as an input to the analog lowpass filters 210, 224.
[0088] Figures 13 and 14 provide further information regarding the unfiltered bipolar transmit
waveform 244. As shown in Figure 13, this waveform displays excursions from +1 to
-1 in an arbitrary amplitude scale, and it includes four cycles at a frequency of
2.5 MHz. Figure 14 shows the frequency spectrum 246 of the bipolar transmit waveform
244 of Figure 13. Note that maximum ultrasonic power is exhibited at the fundamental
frequency (2.5 MHz), and that there is substantial power reduction (greater than -30
dB) at harmonics of the fundamental, such as 5 and 7.5 MHz.
[0089] Figures 15 and 16 are corresponding graphs for the filtered bipolar transmit waveform
supplied as an output of the analog lowpass filter 210, 224 of Figures 10 and 11 and
the summer 223 of Figure 11 a. This filtered bipolar transmit waveform is identified
as reference numeral 248, and includes four cycles with a fundamental frequency of
2.5 MHz. As shown in Figure 16, the frequency spectrum 250 of the waveform 248 has
substantially reduced power (by greater than 30 dB) at all frequencies greater than
about 3.6 MHz.
[0090] Figure 17 provides a filter transfer function for a five pole Butterworth filter
(F
c=3.75 MHz) that can be used for the lowpass filter 210, 224. This transfer function
252 reduces ultrasonic power at the harmonic 5 MHz with respect to the fundamental
2.5 MHz by more than 10 dB, and by about 13 dB in this example.
[0091] Of course, it will be understood by those skilled in the art that the voltage applied
to the transducer elements in the beamformers 200, 220, 220' of Figures 10-11a described
above will typically also be a function of transducer element number. Typically, apodization
is employed so that end transducer elements are operated at a lower voltage than are
the center transducer elements. This may be achieved by switching the high voltage
input to the pulse amplifiers 206, 208 or by adjusting the gain select input for the
amplifier 226 to different voltage levels according to the element position of the
transducer element in the array. For example, the adjustable amplifier 226 can be
a voltage controlled amplifier and the voltage control can be determined by apodization
requirements.
[0092] Figures 18-23 relate to switched filter circuits that may be used in a method or
a system for ultrasonic imaging in which ultrasonic energy is transmitted at a fundamental
frequency to a target, and reflected ultrasonic energy at a harmonic of the fundamental
frequency is received for imaging.
[0093] As shown in Figure 18, the filter circuit 300 defines two signal paths. The first
signal path proceeds from the input 302 via the conductor 306 to the output 304. The
second signal path proceeds from the input 302 via the conductor 308 to the output
304. In this embodiment the second signal path includes a filter 312 and a isolation
circuit 314.
[0094] The input 302 is intended to be coupled to the output of a ultrasonic transmitter,
which can operate to generate unipolar, bipolar or shaped waveforms having substantial
energy at the fundamental frequency. The output 304 of the filter circuit 300 is intended
for connection either directly or indirectly to an ultrasonic transducer. For example,
the output 304 may be coupled (either directly or indirectly) to a transducer connector
or to a transducer cable. Similarly, the output 304 may be coupled to the input of
an ultrasonic receiver as shown in Figure 18, to a receiver protection circuit (not
shown) or to a transmit/receive switch (not shown).
[0095] A switch 310 is controlled to select either the conductor 306 or the conductor 308.
In a first mode of operation the switch 310 is positioned as shown in Figure 18, and
the transmitter is coupled to the transducer via the first signal path including the
conductor 306. In this mode of operation the filter 312 is by-passed. In a second
mode of operation the switch 310 can be placed by the control in connection with the
conductor 308, and transmit signals from the transmitter to the transducer then pass
through the filter 312 and the isolation circuit 314.
[0096] The filter 312 can be any suitable filter designed to suppress energy at the harmonic
of interest. For example, the filter 312 can be a band reject filter centered about
the second harmonic (or other desired harmonic such and third harmonic) of the fundamental
frequency. Alternately, the filter 312 can be a bandpass filter centered on the fundamental
frequency or a low pass filter.
[0097] The isolation circuit 314 is not required in all embodiments. However, it provides
the advantage of avoiding electrical loading of the transducer elements or of the
receiver input stage. Such loading is acceptable, but better performance may be obtained
using the isolation circuit 314 in many cases.
[0098] The filter circuit 320 of Figure 19 is similar to that of Figure 18, except two switches
330, 331 are provided, operated in parallel by the control. When the switches 330,
331 are positioned as shown in Figure 19, the input 322 is connected via the conductor
326 to the output 324, and both the filter 332 and the isolation circuit 334 are completely
isolated from the signal path. When the switches 330, 331 are in the opposite position,
in which the selected signal path includes the conductor 328, signals passing from
the transmitter to the transducer are passed through the filter 332 on the isolation
circuit 334.
[0099] In Figure 19 the receiver input is connected adjacent the input 332, and the switches
330, 331 can automatically be controlled such that they are placed in the state shown
in Figure 19 during receive operations and are automatically switched to the opposite
state for transmit operations.
[0100] The filter circuit 340 of Figure 20 is similar to the circuit 300 of Figure 18, with
two exceptions. In this case the switch 350 has been placed adjacent the input 342,
and the isolation circuit 354 has been moved adjacent the output 344. Thus, signals
pass through the isolation circuit 354 regardless of whether the switch 350 routes
transmit pulses via the conductor 346 or via the filter 352 and the conductor 348.
[0101] As shown in Figure 21, a filter circuit 360 can be provided which provides two signal
paths including conductors 366 and 368, respectively, between an input 362 and an
output 364 for each of 128 channels. The following discussion refers only to channel
1, but the other channels are configured similarly. In this case the filter circuit
360 includes a 128 channel 1:2 multiplexer 370 that switches the transmitter signal
applied to the input 362 either to output terminal 1 (connected to conductor 366)
or to output terminal 129 (connected to filter 372, isolation circuit 374 and conductor
368). Thus, in a first mode of operation of the multiplexer 370, transmitter output
signals on each of 128 channels are routed via the respective inputs 362 and the respective
conductors 366 to the respective outputs 364, thereby bypassing the filters 372 and
the isolation circuits 374. In a second mode of operation as selected by the control,
transmit signals are routed from the inputs 362 via the respective filters 372, isolation
circuits 374, and conductors 368 to the respective outputs 364, thereby placing the
filters 372 and the isolation circuits 374 in the signal paths.
[0102] In any of the examples ― of Figures 18-21 the isolation circuits can be eliminated,
they can be placed as shown in Figure 20 in a common portion of the first and second
signal paths, or they may be placed as shown in Figures 18, 19 and 21 in only one
of the signal paths. Also as shown in Figures 18-21 the receiver can if desired be
connected to the combined signal paths either upstream or downstream of the filter.
In the event the receiver is connected upstream of the filter as shown in Figure 19,
the switch or switches should be controlled to prevent the filter from operating in
the receive mode, at least in those cases where the receiver is responsive to harmonic
ultrasonic energy. In cases such as Figure 18 where the receiver is connected to the
signal path downstream of the filter, the switch 310 can be controlled to bypass the
filter 312 selectively, as for example when the transmitter is used in an alternative
mode of operation in which both the transmitter and the receiver are centered at the
same fundamental frequency. As shown in Figure 21, the switches for the filters may
be part of a pre-existing transducer multiplexer.
[0103] Figure 22 is a schematic diagram of a filter circuit 380 that is similar to the filter
circuit 320 of Figure 19 with two exceptions. First, the filter circuit 380 does not
include an isolation circuit. As explained above, such isolation circuits are optional.
Second, the filter circuit 380 includes a total of three signal paths 386, 388, 389
between the input 382 and the output 384. The switches 390, 391 route signals from
the transmitter to the output via anyone of these three signal paths. The signal path
386 includes no filter while the signal paths 388, 389 include separate respective
filters 392, 393. The filters 392, 393 may for example be band pass filters appropriate
for two different fundamental frequencies. In some applications, the unfiltered signal
path 386 can be eliminated.
[0104] The filter circuit 400 of Figure 23 includes a filter circuit 406 interposed between
an input 402 and an output 404. In this case the filter circuit 406 includes component
filters 408, 410, and a switch 412 is used to connect the signal path containing the
desired one of the component filters 408, 410 to the filter circuit 406. In this way,
the filter characteristics of the filter circuit 406 can be adjusted as appropriate
for the particular application by controlling the switch 412 to select the appropriate
one of the filters 408, 406. As used herein, the term "filter" is intended broadly
to encompass both filter circuits such as low pass, band pass, or band blocking filter
circuits as well filter components such as capacitors, inductors and other electrical
components that affect the filter characteristics of a filter circuit.
[0105] Switched filters similar to any of those shown in Figures 18-23 may be used in the
systems shown in Figures 2, 8, 9, 10, 11 and 11a. For example, switched filters (using
any of the approaches described above) may be substituted for the unswitched filter
58 of Figure 2, the filter 104 of Figure 8, the filter 124 of Figure 9, the filter
210 of Figure 10, the filter 224 of Figure 11, or the filters 232, 234 of Figure 11a.
[0106] In the systems described above, bi-polar rectangular or uni-polar transmit waveforms
may also be shaped. The amplitude of each transmit waveform is shaped to gradually
rise to a maximum value and gradually decrease from the maximum value. Each transmit
waveform is shaped by modulating a carrier waveform with an envelope waveform. Alternatively
and with respect to transmitting a uni-polar waveform, a shaped low pass off-set waveform
with a gradually increasing and decreasing amplitude is summed with a bi-polar waveform
in real-time or off-line. Shaping the amplitude of bi-polar rectangular or uni-polar
transmit waveforms to reduce energies associated with harmonic frequencies is discussed
in U.S. Application No. (unassigned-Attomey Docket No. 5050/220) for Ultrasonic Imaging
Method And System For Transmit Signal Generation For An Ultrasonic Imaging System
Capable Of Harmonic Imaging filed concurrently herewith.
[0107] As yet another alternative arrangement the transmit waveforms discussed above may
be pulse width modulated. As disclosed in U.S. Application No. (unassigned-Attomey
Docket No. 5050/218) for Ultrasonic Imaging Method and Apparatus For Generating Pulse
Width Modulated Waveforms With Reduced Harmonic Response, filed concurrently herewith,
the duration of each pulse within a burst is selected to reduce the energy transmitted
at harmonic frequencies. In particular, the duration of one or more pulses is different
than other pulses within the burst. Preferably, the widths of the pulses within the
burst gradually increase and then decrease, but other duration patterns may be used.
[0108] Alternatively the transmit waveforms discussed above may be shaped as a function
of summation of the waveforms in the acoustic domain. As disclosed in U.S. Application
No. (unassigned-Attomey Docket No. 5050/219) for Ultrasonic Imaging Method And System
For Harmonic Imaging Pulse Shaping In The Acoustic Domain, filed concurrently herewith,
the transmit waveform associated with a first transducer element or elements is shaped
relative to a second waveform associated with a second transducer element or elements.
For example, the first waveform (1) is delayed by a fraction of a cycle or one or
more cycles, (2) is adjusted in amplitude, (3) is transmitted for a different number
of cycles or (4) any combination of two or all three of (1), (2), and (3) relative
to the second waveform. The first and second waveforms are focused at a point and
transmitted. The transmitted waveforms sum in the acoustic domain at the point to
form the desired waveform for reduction of energies transmitted in the harmonic frequencies.
Preferably, the desired waveform corresponds to an amplitude that rises gradually
to a maximum value and decreases gradually from the maximum value.
[0109] As an example of generating transmitted waveforms as a function of the resulting
summed signal in the acoustic domain, the first and second waveforms are rectangular
waves. The first waveform is delayed, in addition to any focusing delay, by may be
¼ of a cycle relative to the second waveform. At the point in the body, the first
and second waveform sum together to form a third waveform. The third waveform has
three amplitude levels (0,1,2). The greatest amplitude is associated with an overlap
of the first and second transmit waveforms and is preferably at the center of the
third waveform. The number of cycles and amplitude shape of the first and second waveforms
may also be controlled to create the desired third waveform in the acoustic domain.
[0110] Any of the various alternatives discussed above, such as pulse width modulation,
filtering, generation of waveforms with multiple amplitudes and summation of waveforms
in the acoustic domain, may be used in combination. The combination may include more
than two of the alternatives discussed above.
[0111] All of the harmonic imaging techniques described above can be used in both tissue
and contrast agent harmonic imaging modes. In the tissue harmonic imaging mode no
additional non-linear contrast agent is added to the target, and only the native non-linear
characteristics of the tissue are relied on to create the ultrasonic image. Medical
ultrasound imaging is typically conducted in a discrete imaging session for a given
subject at a given time. For example, an imaging session can be limited to an ultrasound
patient examination of a given tissue of interest over a period of % to 1 hour, though
other durations are possible. In this case no additional non-linear contrast agent
is introduced into the tissue at any time during the imaging session. In the contrast
agent harmonic imaging mode, any one of a number of weii known non-linear contrast
agents such as those described above can be added to the target in order to enhance
the non-linear harmonic response of the tissue. For this reason, it should be understood
that the introduction of an added non-linear contrast agent into the tissue being
imaged is not implied in any of the following claims unless such added non-linear
contrast agent is expressly recited.
[0112] From the foregoing, it should be apparent that improved systems and methods for imaging
contrast agent have been disclosed. These systems can use the transmit beamformers
described in U.S. Patent 5,608,690, which focuses different frequency components at
different ranges. Also, as described above, these techniques can be used with other
beamformers which utilize other transmit waveforms. Of course, the various aspects
of this invention relating to harmonic suppression and line focus (or other spreading
of the region of maximum intensity) can be used separately from one another, rather
than in combination as described above.